Materials formable in situ within a medical device

ABSTRACT

Certain embodiments of the invention include forming a material in situ by introducing into a space within a patient a water soluble polymer precursor of at least about 10,000 molecular weight solubilized in a flowable aqueous solution. Functional groups on the polymer precursor undergo covalent bonding in situ to form a solid and nonbiodegradable material having a swellability less than about 20% v/v and a Young&#39;s modulus of at least about 100 kPa within about 30 seconds to about 30 minutes of initiating a chemical reaction of the functional groups to form the solid material.

FIELD OF THE INVENTION

The field of the invention relates to flowable precursors that formsolid materials within an implanted medical device, for example anarterial prosthesis placed inside a natural blood vessel to treat ananeurysm.

BACKGROUND

Abdominal Aortic Aneurysms (AAA) are weakened areas in the aorta thatform balloon-like bulges, or sacs, in approximately the abdominal area.As blood flows through the aorta, the pressure of the blood pushesagainst the weakened wall, causing it to enlarge. Blood pools in theenlarged area, usually without forming a firm clot. AAA is usually theresult of degeneration in the media of the arterial wall, resulting in aslow and continuous dilatation of the lumen of the vessel. Ruptured AAAis about the 13th-leading cause of death in the United States, causingan estimated 15,000 deaths per year. While more than 500,000 Americanshave been diagnosed with aortic aneurysms, less than 100,000 are treateddue to shortcomings of current devices and the risk of open surgicalprocedures.

Clips and open surgery have been the traditional interventionaltreatments for AAA. More recently, less invasive techniques have beenattempted, such as introducing a coil into the aneurysm that triggersblood clotting. Of those AAA's that are repaired, only about 30,000procedures are minimally invasive. Other approaches have involvedplacing endografts across the aneurysm, so that blood can flow throughthe lumen of the graft and reduce the pressure on the aneurysm wall toprevent its enlargement and rupture. Stents have been used with theendografts to facilitate their placement and stabilize them in thepatient. Conventional endograft devices, however, can be a poor fit foraneurysms, which can have complex three-dimensional geometries. Further,aneurysms can change shape over time leading to failure of an implantedgraft and/or stent.

SUMMARY

What is needed is a technique for stabilizing AAA-treating devices.These techniques are described herein, including materials and methodsof stabilizing implanted medical devices by introducing flowableprecursor materials that expand an expandable member of the device toset the device in place, with the precursors then hardening to keep thedevice in place. A flowable filler creates the opportunity to expand anexpandable member with adequate pressure to force the member against thesurrounding tissue to conform to the shape of the tissue to create agood fit in a patient. Subsequent hardening of the filler locks thedevice in place. In the case of an AAA, an endograft equipped withsuitable expandable members may be securely positioned with a lumen orlumens that allow blood to flow through the aorta and isolation of theaneurismal sac. The aneurismal sac, without blood flowing into it, isless likely to rupture and may remodel to a less dangerous condition,e.g., by collapsing around the endograft that bridges the sac. Otherexpandable and fillable devices for treating an AAA are described, forinstance, in U.S. Pat. No. 6,312,462, in U.S. Pat. Pub. No. 2004/0204755published Oct. 14, 2004, and in U.S. Application Serial No.US2006/0025853A1 filed on Jul. 22, 2005 which are hereby incorporatedherein by reference to the extent that they do not contradict explicitdisclosure of this specification. As explained below, a filler for anexpandable member should have certain characteristics.

Accordingly, certain embodiments of the technique are directed to amethod of forming a material in situ in a biocompatible expandablemember comprising, for instance, increasing a volume of an expandablemember of a medical device within a patient by delivering a watersoluble polymer precursor in a flowable aqueous solution into theexpandable member. Functional groups on the polymer precursor undergo asingle or combined mechanisms, such as covalent bonding, ionic complex,thermal transition, to form a solid and nonbiodegradable material havinga swellability of less than about, e.g., 20% v/v and having a Young'smodulus of at least about 1 kPa or at least about 10 kPa or at leastabout 100 kPa or at least about 1 MPa or at least about 10 MPa withinabout 30 seconds to about 30 minutes of initiating a chemical reactionof the functional groups to form the solid material, e.g., by freeradical initiation or mixing another precursor having reactivefunctional groups with the first precursor. In some embodiments, thepolymeric precursor comprises at least 100 MW or at least 4,000 MW ofpolyethylene oxide and acrylate functional groups. One variationincludes using two precursors with molecular weights that are differentby a factor of about 10, with the smaller precursor optionally having amolecular weight of less than about 2000 or less than about 1000.Materials formed by these techniques may have aqueous solvent intermixedtherein, and may include intermixed buffering agents. Another variationincludes changing the concentration of reactant solutions to obtain thehardened material.

Some embodiments of the invention relate to a medical device comprisingan expandable member that comprises an aqueous buffered solution and asolid and nonbiodegradable polymeric material having a Young's modulusof at least about 10 kPa or at least about 100 kPa or at least about 1MPa or at least about 10 MPa and a swellability of less than about,e.g., 20% v/v. An aqueous buffered solution or components of such asolution may be dispersed through the material or partially partitionedfrom the material.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1A depicts a polymer precursor with two functional groups.

FIG. 1B depicts two types of polymer precursors with chemically distinctbackbones and similar functional groups.

FIG. 1C depicts a polymer precursor with two types of functional groups.

FIG. 1D depicts a multi-armed polymer precursor with four functionalgroups.

FIG. 1E depicts two polymer precursors of different molecular weights.

FIG. 1F depicts a multi-armed polymer precursor with two types offunctional groups.

FIG. 1G depicts two polymer precursors with two types of functionalgroups.

FIG. 2 depicts a polymer precursor with a polyethylene glycol backboneand acrylate functional groups.

FIG. 3 depicts a polymer precursor with a polyethylene glycol backboneand methacrylate functional groups.

FIG. 4 depicts a polymer precursor with methacrylate functional groups.

FIG. 5 depicts a polymer precursor with a polypropylene backbone andmethacrylate functional groups.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS OF THE INVENTION

One embodiment of the invention is a system for forming polymericmaterials in situ within an implantable medical device. As explainedabove, some implants can be stabilized in the body by introducing animplant with an expandable member that can be inflated with polymerprecursors that form a solid material. The polymer precursors andresultant solid material may be chosen in light of a variety ofconsiderations, including solubility in aqueous solution, viscosity,reaction time, heat of polymerization, shelf life, pot life, bonding tothe medical device, and mechanical properties after polymerization suchas tensile strength, low-swellability, compressive strength, stiffness,elasticity, brittleness, stability, and durability. Functional groups onthe precursors may be chosen to address these and other designconsiderations. Other components of the system may be chosen to adjustthese characteristics or to provide additional control over otherpertinent factors, e.g., pH, durability, radiopacity, bonding toplastic, bonding to metal, and biocompatibility.

For treatment of AAA, an endograft comprising a thin, double-walledballoon can be placed across the AAA with an inner lumen of theendograft providing for blood flow through the endograft. The balloon isfilled in-situ with flowable polymeric precursors that polymerize andharden into a solid material. The hardened material is conformed to thespecific shape of the patient's aneurysm and provides stability, aleakproof seal, and prevents migration of the endograft.

The polymer precursor is a polymer that has reactive functional groupsthat form covalent bonds with particular functional groups on otherpolymer precursors to thereby form a polymeric material. The polymerprecursor may be any polymer or a synthetic polymer. Synthetic is a termthat refers to molecules not naturally produced by a human cell andexcludes, for example, collagen regardless of how it is made or how itis chemically modified. Some polymer precursors may be essentiallysynthetic meaning that they are at least about 90% by molecular weightsynthetic with the balance of the precursor being chemical groups with abiological motif, e.g., a sequence of amino acids degradable byparticular enzymes. Polymer precursors may be selected to be free ofamino acids, or peptide bonds, or saccharide units, or polysaccharides.

Polymer precursors may comprise a variety of polymeric groups. Someprecursors are water soluble, meaning that the precursors are soluble inaqueous solution at a concentration of at least about 1 gram per liter.Some precursors comprise polyethylene oxide (PEO, —(CH₂CH₂O)_(n)—),which is useful to impart water solubility and desirable viscosity insolution and mechanical properties when formed into a polymericmaterial. Some polymer precursors comprise, e.g., about 100 to about500,000 MW of PEO; the ordinary artisan will understand that all valuesand subranges within these explicitly articulated values are included,e.g., about 600 Daltons, about 15,000 Daltons, about 500 to about100,000 Daltons, about 5,000 to about 50,000 Daltons. Some precursorsinclude comparable amounts of polymers related to PEO, e.g.,polypropylene oxide (PPO, —CH₂(CH₂)₂O)_(n)—), other polyalkylene oxide,or a copolymer of PEO-PPO, e.g., about 100 to about 250,000 Daltons.Water-soluble precursors may also be formed directly from, or afterderivitization of, other polymers, e.g., poly(acrylic acid), poly(vinylalcohol), polyvinyl chloride, polyacrlonitrile, polyallyamine,polyacrylates, polyurethanes, polycarbomethylsilane,polydimethylsiloxane, polyvinylcaprolactam, polyvinylpyrrolidone, or acombination of these. For example, a nonwater soluble polymer may bedecorated with water soluble groups to enhance its water solubility tomake a water soluble polymer precursor, e.g., by adding carboxyls,hydroxyls, or polyethylene glycols. Examples of water soluble monomersthat may be used to are 2(2-ethoxyethoxy) ethyl acrylate, ethoxylated(15) trimethylolpropane triacrylate, ethoxylated (30) bisphenol adiacrylate, ethoxylated (30) bisphenol a dimethacrylate, ethoxylated(20)trimethylolpropane triacrylate, metallic diacrylate, methoxypolyethylene glycol (350) monoacrylate, methoxy polyethylene glycol(350) monomethacrylate, methoxy polyethylene glycol (550) monoacrylate,methoxy polyethylene glycol (550) monomethacrylate, polyethylene glycol(200) diacrylate, polyethylene glycol (400) diacrylate, polyethyleneglycol (400) dimethacrylate, polyethylene glycol (600) diacrylate,polyethylene glycol (600) dimethacrylate, and polypropylene glycolmonomethacrylate.

Polymer precursors may be linear or be branched. For example, theprecursor may have 3 or more termini, e.g., at least 3, or about 3 toabout 12, artisans will immediately appreciate that all ranges andvalues within the explicitly stated ranges are disclosed. A variety oftechniques and sources for obtaining multi-armed precursors andattaching functional groups to them are known, e.g., as in the Aldrichcatalog or Nektar or Shearwater Polymers or from Sartomer, Inc.catalogs, as well as in the literature for these arts.

Some embodiments include two or more precursors with distinct averagemolecular weights or two or more types of precursors. Different types ofprecursors have distinct chemical formulae. A single type of polymer maybe incorporated into two polymeric precursors having two distinctaverage molecular weights. Molecular weight averages for a solution ofprecursors may be determined as is customary in these arts, e.g., byweight or number averaging. Accordingly, a molecular weight for aprecursor represents an average molecular weight for a plurality ofprecursors.

A precursor's functional groups may be, for example, polymerizable orreactive by electrophile-nucleophile combination. The groups may bereactive with identical groups, e.g., as in free radical polymerizationof acrylates, or with complementary groups, e.g., as inelectrophilic-nucleophilic reactions. Polymerizable groups include,e.g., ethylenically unsaturated groups, groups polymerizable byfree-radical chemistry, condensation chemistry, or addition chemistry.Examples of functional groups are: acrylates, methacrylates, butylacrylate, methyl methacrylate, butyl methacrylate, hydroxyethylmethacrylate, polypropylene glycol diglycidal ether, polyethylene glycoldiglycidyl ether, N-acryloxysuccinimide, glycidyl methacrylate, andhexamethylene diisocyanate. Examples of electrophilic or nucleophilicfunctional groups include succinimide esters, maleic acids, isocyanates,maleic acids, carbodiimides, aldehydes, azos, diazos, thiocyanates,carboxyls, amines, thiols, and hydroxyls. The functional groups on aprecursor may be the same or of different types, with each type offunctional group being a chemically distinct group. Different types ofprecursors may have the same or different types of functional groups,provided that the precursors react to form a polymeric material.

In some embodiments, acrylates may advantageously be used becauseacrylates are generally water soluble but do not react with water. Incontrast, for example, a polyurethane precursor will react with water.Also, acrylamide monomers are generally toxic, while water solubleacrylates have a low toxicity and are more acceptable for biomedicalapplications involving implantation.

For example, FIG. 1A depicts a polymer precursor with two functionalgroups that have the same chemical formula, with the functional groupsbeing reactable to form a solid material, e.g., by free radicalpolymerization. And FIG. 1B shows two types of polymer precursors withchemically distinct backbones that both have the same type of functionalgroup, with the two precursors being reactable with each other to form asolid material. FIG. 1C depicts a set of polymer precursors withdifferent functional groups that can react to form a solid material,e.g., by free radial polymerization or electrophilic-nucleophilicreaction. Other variations include, for example, a multi-armed precursorterminated with the same type of functional group (FIG. 1D), a set ofprecursors with similar backbones of different molecular weight andhaving the same functional groups (FIG. 1E), a multi-armed precursorwith different types of functional groups, e.g., for free radicalpolymerization or electrophilic-nucleophilic reaction (FIG. 1F), or aset of precursors with distinct functional groups (FIG. 1G). FIG. 2depicts an exemplary polymer precursor having a PEG backbone andacrylate functional groups. FIG. 3 depicts an exemplary polymerprecursor having a PEG backbone and methacrylate functional groups. FIG.4 depicts an exemplary polymer precursor having methacrylate functionalgroups reacted with a diglycol. FIG. 5 depicts an exemplary polymerprecursor having a polypropylene backbone and methacrylate functionalgroups

Some embodiments employ combinations of polymer precursors with largevariations in molecular weight. A small precursor can be relatively moremobile than an end of a larger precursor so that fewer living chains areterminated without reaction. Further, a small precursor can be used tocontrol physical properties of a material generated from the largerprecursor, e.g., to adjust stiffness or other properties controlled bythe number and distance between chain crosslinks. For instance, a lowermolecular weight precursor can enhance the stiffness of a polymericmaterial by providing shorter distances between crosslinks. Thus someembodiments include a first precursor with a molecular weight of about30,000 to about 300,000 and a second precursor with a molecular weightbetween about 100 and about 3,000. Other embodiments use a precursorwith a molecular weight that is about 10 to about 100 times less thanthe molecular weight of a second precursor or, alternatively, less thanthe molecular weight of all the other precursors in the system. Forinstance, a first precursor having free radical polymerizable functionalgroups can be mixed with a relatively lower molecular weight precursorhaving free radical polymerizable functional groups. When polymericprecursors are reacted, they form polymer segments in the polymericmaterial. Thus a 30,000 MW bifunctional polymer precursor can form apolymer segment of 30,000 MW in the material.

The time required for polymer precursors to react may be controlled bythe choice of functional groups, precursor size, pH, initiator,catalyst, or accelerants. In general, a time of between about 30 secondsto about 30 minutes for polymerization is desired so that the precursorsolution or solutions may be introduced into the medical device withoutundue increases in viscosity and without unduly extending the proceduretime required for the precursors to form a firm material that permitsusers to close the patient. The time to polymerization may be measuredoutside a patient by observing the time from activation of precursors ina solution or suspension until the solution or suspension is no longerflowable. Activation of the precursors refers to the event that triggerstheir reaction with each other, e.g., initiating a free radicalpolymerization or mixing electrophilic and nucleophilic groups at areactive pH.

Bonding of the polymeric material to the device may be controlled byselecting precursor functional groups and/or precursors to bond theexpandable member, or members that receive the precursors or mixedprecursors. Bonding to plastic and metal may be enhanced by usingsuitable functional groups, e.g., sodium acrylates or other metallicacrylates.

The material formed upon reaction of polymer precursors should haveadequate mechanical properties to keep the device stable within thepatient. Thus materials that are stiff enough to resist deformationcaused by forces applied to the device after implantation areadvantageous. Embodiments include materials with a Young's modulus of atleast about 500 kPa, or 1000 kPa, or in a range of about 500 kPa toabout 50,000 kPa; artisans will immediately appreciate that other valuesmay be suitable and that all values and ranges within the explicitlyarticulated ranges are disclosed. Modulus is measured as follows:Cylindrical shaped samples of the crosslinked polymer are created byinjecting the polymeric mixture into a silicone tubing of a known innerdiameter. After time required to substantially complete crosslinking haselapsed, 1 cm high cylindrical “discs” are cut from the tubing using asharp razor blade; alternatively, tubing of 1-cm in length is used sothat no cutting is necessary. The discs are carefully removed, avoidingcracking the samples and ensuring they are free of bubbles and edgedefects. The discs are then subjected to a crush test in an Instronuniversal materials testing machine using a flat compression plate andusing a 500N load cell. The modulus can be calculated using theextension and load data obtained during the preloading step where thestress strain curve is linear. The Load (N) divided by the plug crosssectional area (in meters square) gives the stress (Pa), while theamount of preload compression (Extension, mm) divided by the plug length(mm) gives the strain (no units). Modulus can then be calculated bydividing Stress with Strain. The ultimate strain can be computed asfollows:

-   -   Ultimate percent strain is then total plug compression divided        by plug length, times 100.

Total plug compression (mm)=Extension (mm)+displacement (mm)

Percent strain=[Total plug compression (mm)/plug length (mm)]*100

The maximum stress attained is the ultimate stress.

Certain embodiments are non-hydrogels. Certain embodiments are polymersformed from the precursors and functional groups set forth herein, aswell as combinations thereof, e.g., polyacrylates, polymethacrylates,and polymethylmethacrylates. Materials that have a high ultimate stressand strain and which still have a modulus above about 100 kPa) arepreferred. Materials that do not show substantial hydration upon beingplaced in an aqueous environment and also do not exhibit substantialdegradation in physical properties over time are preferred.

The material formed upon reaction of polymer precursors should haveadequate durability to keep the device stable within the patient overtime. Some embodiments of the material effectively maintain theirmechanical properties over a period of at least 5, 10, 15, 20, or 30years. Some embodiments of the polymeric material are essentially notbiodegradable in an animal body, i.e. are not subject to effectivehydrolytic and/or enzymatic degradation that leads to a loss ofmechanical strength in an animal body in a typical tissue, i.e., asmeasurable by implantation subcutaneously, intramuscularly, orintravascularly in an animal model such as a rat or a rabbit. Examplesof nonbiodedgrabale polymeric materials are polyacrylates,polymethacrylates, and polymethylmethacrylates. Examples ofbiodegradable materials are fibrin glue, hyaluronic acid, collagen,polylactic acid, and many polyesters.

The polymeric material may be designed to have limited swellability inaqueous solution. A limited degree of swelling advantageously preventsthe polymeric material from applying pressure to its surroundings afterformation, even if water is present. And limited intake of water throughswelling can help to keep the material immobile in the patient. Certainembodiments of the polymeric materials have a swelling in aqueoussolution of less than 20% v/v, 10% v/v, 5% v/v, or 1% v/v, as measuredby exposing the polymeric material to a 300-330 milliOsmolar, pH 7.4buffered water solution after the polymeric material essentially reachesits full compressive strength and observing its change in weight afterit has been allowed to swell in an unconstrained state for 24 hours,with the volume swelling being calculated from the change in weight.

Viscosity of solutions of the polymer precursors can be controlled byadjusting factors such as the type of polymer, the polymerconcentration, solubility of the polymer, and the polymer's molecularweight. In general, the viscosity of a precursor solution should be lowenough to allow the solution to be forced down a tube, e.g., a hollowtube guidewire, that allows inflation of an endograft using medicallysafe pressures. Some medical devices use such tubes to inflate balloonson endoscopic devices, e.g., for angioplasty or temporary occlusion of ablood vessel. In general, viscosities of less than about 500 centipoise,less than about 100 centipoise, or less than about 10 centipoise, arepreferable. The viscosity may be adjusted for use inconventionally-sized tubes, with conventional operating pressures ofless than about 25 atmospheres.

Some embodiments of the precursors are chosen with functional groupsthat are reactable at an approximately physiological pH and/orosmolarity. These characteristics are useful, for instance, foremploying physiological buffers to solubilize the precursors, push theprecursors into place, or to flush a portion of the device withprecursors or polymeric material in place. When two or more solutions ofprecursors are mixed, buffers for one or more of the solutions may bechosen to have a first pH before mixing and a second pH after mixing.For example, a first precursor solution may have a low pH in a lowbuffering strength buffer to minimize reaction of the precursors and asecond solution with a relatively higher buffering strength may be mixedwith the first solution to achieve a second pH that is favorable forreaction of the precursors. Additionally, the ester linkages areobserved to be more stable at somewhat acidic pH (e.g., about pH 4) andso a particular pH may be selected for certain components for reasons ofstability. Upon implantation, a physiological pH of (e.g., about 7 toabout 8) may be chosen for biocompatibility reasons. Alternatively adifferent pH may be chosen, e.g., from about 4 to about 9.

Radio-opaque components may be introduced with polymeric precursors toallow visualization of the polymeric material after it is formed.Examples of radio-opaque materials are PANTOPAQUE, barium sulfate,tantalum powder, (all water insoluble), ISOVUE, OXILAN, iodapamide,omnipaque, metrizamide, iopentol, iohexol, iophenoxic acid, ioversol,gadodiamide, and sodium tyropanoate. Components may be introduced toenhance imaging, for example, according to X-ray, magnetic resonanceimaging, and tomography, e.g., spiral computer tomography techniques.

Some embodiments of the functional groups are free radical polymerizablegroups that may advantageously be exposed to initiators and/or catalyststo, for example, enhance reaction kinetics or mechanical properties ofthe polymeric material.

Initiators are required to start polymerization in many systems, andinclude, for example, thermal, chemical, and light-activated initiators.Initiators may be used to activate the polymer precursors to polymerizeand form the polymeric material. Initiator concentration can affectvariables such as polymerization time, temperature, and mechanicalproperties of the polymeric material.

In reduction-oxidation chemical initiating systems, for example, metalions may be used either as an oxidizer or a reducer. For example,certain metal ions may be used in combination with a peroxide orhydroperoxide to initiate polymerization. Some suitable metal ions haveat least two states separated by only one difference in charge, e.g.,ferric/ferrous; cupric/cuprous; ceric/cerous; cobaltic/cobaltous;vanadate V vs. IV; permanganate; and manganic/manganous. Peroxygencontaining compounds, such as peroxides and hydroperoxides, includinghydrogen peroxide, t-butyl hydroperoxide, t-butyl peroxide, benzoylperoxide, cumyl peroxide, may also be used.

Thermal initiating systems may also be used, for example, commerciallyavailable low temperature free radical initiators that initiate freeradical crosslinking reactions at or near physiological bodytemperatures. Some examples are sodium persulfate (50° C.), ammoniumpersulfate (50° C.), glucose oxidase-glucose-ferrous sulfate (initiatedaround 37° C. in presence of dissolved oxygen).

Photoinitiators are also known for initiation of polymerization, e.g.,DAROCUR 2959 (initiated around 360 nm), IRGACURE 651 (initiated around360 nm), eosin-triethanol amine (initiated around 510 nm), methyleneblue-triethanol amine (initiated around 632 nm), and the like.

Catalysts, co-catalysts, and chain extenders may be used to furthercontrol reaction of the polymer precursors or to extend shelf life. Forexample, small amounts of vinyl pyrrolidinone (e.g., around 1-10 μl perml) can be added while using eosin-triethanol photoinitiating system.Inhibitors such as hydroquinone may be added to prevent prematurepolymerization of polymer precursors during storage.Tetramethylethylenediamine (TEMED) is a catalyst useful in manypolymerizations, e.g., in an ammonium persulfate/TEMED orriboflavin/TEMED catalyzed reaction. Some initiators can be chosen thatrequire little or no oxygen, e.g., riboflavin-based initiator systems.Systems that are not substantially inhibited by the presence of oxygenand that can enable the reaction to proceed at physiological temperaturemay be chosen.

Delivery of polymeric precursors in aqueous solution facilitatespreparation of a solution with a controlled viscosity by includingwater. Further, an aqueous solution, as opposed to, e.g., an organicsolvent, provides safety benefits in case some amount of the solutionshould be exposed to the patient or user. The presence of water alsoserves to reduce the mass of polymerizable precursors used, and thusimproves the toxicological profile of the precursors, should they beaccidentally discharged into the body. Further, an aqueous solvent forthe precursors is avoids potential compatibility problems with materialsused in the expandable device, such as degradation of the material orpotentially unwanted changes to its mechanical properties, e.g.,softening by partial salvation. In general, aqueous solutions do notsolvate biomaterials used for an expandable member of a medical device.The aqueous solvent may be interspersed through the polymeric material,e.g., in pore spaces, or some portion of the solvent may be partitionedaway from the material. The solvent may be buffered with a bufferingagent or agents to control pH of the solution. The amount of aqueoussolvent to mix with the other components of the system may be adjustedto achieve a desired viscosity in light of the properties of thehardened material. Some embodiments include between about 0.5 parts toabout 10 parts by weight of polymeric precursor compared to the weightof the aqueous solvent; artisans in this field will immediatelyappreciate that all ranges and values within this range are disclosed.

The polymer precursors may be used to fill an expansion member of animplantable medical device. The medical device may be, for example,suited for minimally invasive surgery (MIS) techniques, e.g., guidablethrough vasculature of a human patient using a guidewire introduced intothe patient for that purpose. Examples of MIS devices having aninflatable or expandable member or are provided in, for example, PCTApplication Pub. No. WO 00/51522, U.S. Pat. Nos. 5,334,024, 5,330,528,6,312,462, 6,964,667, 7,001,431, in U.S. Pat. Pub. No. 2004/0204755published Oct. 14, 2004, and U.S. Patent Serial No. US2006/0025853A1filed on Jul. 22, 2005, which are hereby incorporated by referenceherein to the extent that they do not contradict what is explicitlydisclosed herein.

An expandable member undergoes an increase in volume resulting fromintroduction of a flowable material into the member. An expandablemember may be, for example, a balloon, a double-walled balloon, or aninflatable cuff. The expandable member may include either compliantmaterials, or non-compliant materials, or both. A non-compliant materialgenerally resists deformation under physiological conditions, e.g.,parylene, polytetrafluoroethylene, or polyethylene terephthalate.Examples of compliant materials are silicones, latexes, and elasticmaterials in general. A noncompliant material may be used in anexpandable member by introducing the material in a shape that allows forsubsequent expansion; for example, a noncompliant material be coiled orfolded for delivery and expanded by uncoiling or unfolding, e.g., as aresult of filling the member with a flowable precursor. A balloon usedfor placement of an implantable medical device may be a sealed,flexible, expandable member that is elastic. Balloons may take a widevariety of shapes, e.g., including spherical, ellipsoidal, tubular,cylindrical (filled between double walls with a lumen interior to thecylinder). Expandable members may include a combination of compliantmaterials and noncompliant materials, e.g., a noncompliant portionadjoined to a complaint portion.

In use, polymer precursors in a flowable form may be delivered to anexpandable member wherein they are solidified into a polymeric material.The flowable precursors may be introduced into the expansion member toexpand a flexible material to increase a volume of the member, which maybe sealed after it is expanded. The material within the member is may bereferred to as being within the patient even though the material doesnot directly contact a patient's tissue. Expansion of the member mayforce the member against a tissue of the patient to seat the device inthe tissue. Hardening of the precursors into a solid material furthersecures the device. The precursor or precursors may be activated before,during, or after introduction into the expansion member. Activationbeforehand may be accomplished by mixing a polymeric precursor with anactivating agent that causes precursors to form covalent bonds, forexample, as an initiator that initiates polymerization, a buffer thatchanges a pH of a precursor-and-initiator solution to activate theinitiator, or external energy in the form of heat or light may beapplied to activate a thermal or photoinitiator. And, for example,electrophilic-nucleophilic reactions may be activated by mixing aprecursor with electrophilic functional groups with a precursor havingnucleophilic functional groups, or by using a buffer to change the pH ofa premixed combination of precursors with electrophilic and nucleophilicfunctional groups.

In some embodiments, two solutions are mixed with each other ex vivo andintroduced using MIS techniques into an expandable member. The mixtureis pumped through a filling tube into the expandable member until adesired pressure is achieved, and the tubes for filling the member arewithdrawn, leaving the expandable member inflated with the mixture,which is sealed entirely within the member and hardens into a solidmaterial, e.g., a polymeric material, with the time to polymerizationbeing greater than the amount of time required to fill the member andwithdraw the filling tube. An example of this method is combining afirst container having a polymerizable first precursor with a solutionhaving an initiator that initiates polymerization. As explained above,various types and sizes of precursors may be used in combination withvarious types of initiators. For instance, two solutions with differenttypes and/or molecular weights of precursors may be used.

In other embodiments, two solutions are prepared that are separatelyintroduced via separate filling tubes for combination within thepatient, e.g., mixing for the first time in the expandable member or ina manifold disposed in the introductory device.

By way of example, a kit may be prepared with a first precursorcontainer having about 10 grams of a 35,000 MW PEG polymeric precursorterminated with a diacrylate functional group at each of two ends. Thefirst precursor container may contain a radio-opaque agent, e.g., about10 grams sodium diatrizoate, and an initiator, e.g., about 1.8 grams ofa persulfate. A first diluent container has about 230 ml of phosphatebuffered solution at physiological pH (e.g., 7.4) and physiologicalosmolarity, or an osmolarity and buffering strength that achievesphysiological pH and osmolarity after combination with other components.A second precursor container has about 150 ml of essentially pure 600 MWPEG polymeric precursor terminated with a diacrylate functional group ateach of two ends, and further comprises 100 ml of phosphate bufferedsolution pH 4 and a catalyst, e.g., about 1.8 ml of TEMED. A user mixesthe first diluent container with the first precursor container to form afirst precursor solution that is mixed with the contents of the secondprecursor container and used to fill an expandable member. Theprecursors form a hard firm crosslinked material in approximately 2-3minutes. The material is visible on x-ray fluoroscopy due to the sodiumDiatrizoate. As described above, the system may be controlled to producefaster or shorter polymerization time, e.g., from about 30 seconds toabout 30 minutes for either or both. For instance, about 1.2 g ofpersulfate and 1.2 ml of TEMED would provide approximately a 5-6 minpolymerization time. Or about 0.6 g of persulfate and about 0.6 ml ofTEMED in the same formulation would result in a polymerization time ofabout 20 minutes.

As already discussed, other variations include, for example, replacingPEG 600DA with ethoxylated trimethylolpropane triacrylate or ethoxylatedpentaerythritol tetraacrylate, changing solids concentrations, use ofalternative radiopacifiers, using other initiation systems (e.g., ironsalts and hydrogen peroxide), or adding comonomers that promote adhesionto plastic.

Certain other embodiments involve using a filler material mixed withpolymeric precursor(s) to form a polymeric material that includes afiller. A filler can be used to adjust the properties of the polymericmaterial, for example, the stiffness, mechanical strength,compressibility, or density. Examples of fillers include solid objects,e.g., beads, cylinders, microbeads, hollow materials, e.g., hollowmicrospheres, fibers, e.g., polylactic acid fibers, and meshes, e.g.,nylon meshes. Such fillers may be mixed with one or both of theprecursors before introduction into an implant, or the fillers may beadmixed in situ. The precursor solutions may be used as a continuoussuspending medium to hold the filler in place.

1. A method of forming a material in situ in a biocompatible expandable member comprising: increasing a volume of an expandable member of a medical device within a patient by delivering a water soluble polymer precursor in a flowable aqueous solution into the expandable member, wherein functional groups on the polymer precursor undergo covalent bonding to form a solid and substantially non biodegradable material having a swellability of less than about 20% v/v and a Young's modulus of at least about 100 kiloPascals within about 30 seconds to about 30 minutes of initiating a chemical reaction of the functional groups to form the solid material.
 2. The method of claim 1 wherein the polymeric precursor comprises functional groups and at least 100 MW of polyethylene oxide.
 3. The method of claim 1 wherein the functional group comprises an ethylenically unsaturated group.
 4. The method of claim 1 wherein the viscosity of the flowable solution is less than about 500cp.
 5. The method of claim 1 wherein the functional groups are of a first type and further comprising a second type of functional groups on a second polymeric precursor that react to form covalent bonds with the first type of functional groups.
 6. The method of claim 5 wherein the first polymeric precursor has a molecular weight of at least about 10,000 and the second polymeric precursor has a molecular weight of less than about 3,000.
 7. The method of claim 1 wherein the aqueous solution further comprises a buffer and a pH of about 4.0 to 9.0.
 8. The method of claim 1 comprises providing the polymer precursor as a powder and combining the polymer precursor with a buffer and an initiator.
 9. The method of claim 1 wherein initiating the chemical reaction comprises mixing the polymeric precursor with a polymerization initiator.
 10. The method of claim 1 wherein the solution further comprises a catalyst for catalyzing free radical polymerization of the functional groups.
 11. The method of claim 1 wherein the solution further comprises an initiator for initiating the chemical reaction.
 12. The method of claim 1 wherein the solution further comprises a radio-opaque agent for imaging the material.
 13. The method of claim 1 wherein the functional groups are electrophilic or nucleophilic.
 14. The method of claim 1 wherein the functional groups are polymerizable by free radical polymerization.
 15. The method of claim 1 wherein the material has a Young's modulus of at least 1 kPa within 30 seconds to 10 minutes of initiating the chemical reaction of the functional groups.
 16. The method of claim 1 wherein the expandable member comprises a balloon or cuff.
 17. The method of claim 1 wherein the polymeric precursor is present at a range of between about 0.1 parts to about 10 parts by weight of polymeric precursor compared to the weight of the aqueous solvent in the solution.
 18. A method of forming a material in situ comprising: introducing into a space within a patient a water soluble polymer precursor of at least about 400 molecular weight solubilized in a flowable aqueous solution, wherein functional groups on the polymer precursor undergo covalent bonding to form a solid and nonbiodegradable material having a swellability less than about 20% v/v and a Young's modulus of at least about 100 kiloPascals within about 30 seconds to about 30 minutes of initiating a chemical reaction of the functional groups to form the solid material.
 19. The method of claim 18 wherein the polymeric precursor comprises at least 100 MW of polyethylene oxide.
 20. The method of claim 18 wherein the functional group comprises an acrylate.
 21. The method of claim 18 wherein the viscosity of the flowable solution is less than about 100 cp.
 22. The method of claim 18 wherein the functional groups are of a first type and further comprising a second type of functional groups on a second polymeric precursor that react to form covalent bonds with the first type of functional groups.
 23. The method of claim 22 wherein the first polymeric precursor has a molecular weight of at least about 10,000 and the second polymeric precursor has a molecular weight of less than about
 3000. 24. The method of claim 18 wherein initiating the chemical reaction comprises mixing the polymeric precursor with a polymerization initiator.
 25. The method of claim 18 wherein the solution further comprises a radio-opaque agent for imaging the material.
 26. The method of claim 18 wherein the functional groups are electrophilic or nucleophilic.
 27. The method of claim 18 wherein the functional groups are polymerizable by free radical polymerization.
 28. The method of claim 18 wherein the material has a Young's modulus of at least 10 kpa within 30 seconds to 10 minutes of initiating the chemical reaction of the functional groups.
 29. The method of claim 18 wherein the expandable member comprises a balloon or a cuff.
 30. The method of claim 18 wherein the polymeric precursor is present at a range of between about 0.1 parts to about 10 parts by weight of polymeric precursor compared to the weight of the aqueous solvent in the solution.
 31. A medical device comprising an expandable member that comprises an aqueous buffered solution and a solid and nonbiodegradable polymeric material having a Young's modulus of at least about 100 kilopascals and a swellability of less than about 20% v/v, wherein the aqueous buffered solution is dispersed through the material or partially partitioned from the material.
 32. The device of claim 31 wherein the aqueous solution is present at a range of between about 0.1 parts to about 1 part by weight of polymeric precursor compared to the weight of the aqueous solvent.
 33. The device of claim 31 wherein the material comprises polymers comprising 100 MW of polyethylene oxide.
 34. The device of claim 31 wherein the material comprises polyacrylate.
 35. The device of claim 31 wherein the material comprises a reaction product of two types of functional groups.
 36. The device of claim 31 wherein the material comprises a first polymer segment having a molecular weight of at least about 10,0000 and a second polymer segment having a molecular weight of less than about
 1000. 37. The device of claim 31 further comprising a radio-opaque agent for imaging the material.
 38. The device of claim 31 wherein the expandable member comprises a balloon or cuff. 